|Publication number||US7029470 B2|
|Application number||US 10/685,236|
|Publication date||Apr 18, 2006|
|Filing date||Oct 14, 2003|
|Priority date||Apr 26, 2001|
|Also published as||DE60222114D1, DE60222114T2, EP1389966A1, EP1389966B1, US6663627, US7824399, US20020183736, US20040044340, US20060142753, WO2002102263A1|
|Publication number||10685236, 685236, US 7029470 B2, US 7029470B2, US-B2-7029470, US7029470 B2, US7029470B2|
|Inventors||David E. Francischelli, Eduardo N. Warman, Rahul Mehra, Mark T. Stewart, James R. Skarda, Harry Puryear, David Schwartzman|
|Original Assignee||Medtronic, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (26), Referenced by (52), Classifications (35), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of U.S. Ser. No. 10/132,392, filed Apr. 24, 2002 by Francischelli et al, now U.S. Pat. No. 6,663,627, and also claims priority to Provisional U.S. Patent Application No. 60/286,923, filed Apr. 26, 2001 by Francischelli et al., incorporated herein by reference in its entirety.
The present invention relates to tissue ablation devices generally and relates more particularly to devices adapted to ablate lines of tissue, for example for use in conjunction with an electrosurgical version of the Maze procedure.
The Maze procedure is a surgical intervention for patients with chronic atrial fibrillation (AF) that is resistant to other medical treatments. The operation employs incisions in the right and left atria which divide the atria into electrically isolated portions which in turn results in an orderly passage of the depolarization wave front from the sino-atrial node (SA Node) to the atrial-ventricular node (AV Node) while preventing reentrant wave front propagation. Although successful in treating AF, the surgical Maze procedure is quite complex and is currently performed by a limited number of highly skilled cardiac surgeons in conjunction with other open-heart procedures. As a result of the complexities of the surgical procedure, there has been an increased level of interest in procedures employing electrosurgical devices or other types of ablation devices, e.g. thermal ablation, micro-wave ablation, cryo-ablation or the like to ablate tissue along pathways approximating the incisions of the Maze procedure. Electrosurgical systems for performing such procedures are described in U.S. Pat. No. 5,916,213, issued to Hiassaguerre, et al. U.S. Pat. No. 5,957,961, issued to Maguire, et al. and U.S. Pat. No. 5,690,661, all incorporated herein by reference in their entireties. Cryo-ablation systems for performing such procedures are described in U.S. Pat. No. 5,733,280 issued to Avitall, also incorporated herein by reference in its entirety.
In conjunction with the use of electrosurgical ablation devices, various control mechanisms have been developed to control delivery of ablation energy to achieve the desired result of ablation, i.e. killing of cells at the ablation site while leaving the basic structure of the organ to be ablated intact. Such control systems include measurement of temperature and impedance at or adjacent to the ablation site, as are disclosed in U.S. Pat. No. 5,540,681, issued to Struhl, et al., incorporated herein by reference in its entirety.
Additionally, there has been substantial work done toward assuring that the ablation procedure is complete, i.e. that the ablation extends through the thickness of the tissue to be ablated, before terminating application of ablation energy. This desired result is some times referred to as a “transmural” ablation. For example, detection of a desired drop in electrical impedance at the electrode site as an indicator of transmurality is disclosed in U.S. Pat. No. 5,562,721 issued to Marchlinski et al, incorporated herein by reference in its entirety. Alternatively, detection of an impedance rise or an impedance rise following an impedance fall are disclosed in U.S. Pat. No. 5,558,671 issued to Yates and U.S. Pat. No. 5,540,684 issued to Hassler, respectively, also incorporated herein by reference in their entireties. Because ablated heart tissue is necrotic, it does not depolarize and therefore does not contribute to the depolarization signal. This fact has recently led some physicians to use the amplitude of a locally acquired electrogram signal to determine whether a lesion is complete. For example, during provision of R-F energy at a constant power level, the physician may monitor the amplitude of electrograms obtained using electrodes adjacent the ablation site, and, in response to a defined drop, e.g. 75%, may terminate provision of RF energy.
Three basic approaches have been employed to create elongated lesions using electrosurgical devices. The first approach is simply to create a series of short lesions using a contact electrode, moving it along the surface of the organ wall to be ablated to create a linear lesion. This can be accomplished either by making a series of lesions, moving the electrode between lesions or by dragging the electrode along the surface of the organ to be ablated and continuously applying ablation energy, as described in U.S. Pat. No. 5,897,533 issued to Mulier, et al., incorporated herein by reference in its entirety. The second basic approach to creation of elongated lesions is simply to employ an elongated electrode, and to place the elongated electrode along the desired line of lesion along the tissue. This approach is described in U.S. Pat. No. 5,916,213, cited above and. The third basic approach to creation of elongated lesions is to provide a series of electrodes and arrange the series of electrodes along the desired line of lesion. The electrodes may be activated individually or in sequence, as disclosed in U.S. Pat. No. 5,957,961, also cited above. In the case of multi-electrode devices, individual feedback regulation of ablated energy applied via the electrodes may also be employed. The present invention is believed useful in conjunction with all three approaches
The present invention is directed toward an improved system for creating lesions and assessing their completeness or transmurality. In the preferred embodiment as disclosed, the apparatus for producing the lesions is an electrosurgical device, in particular a saline-irrigated bipolar electrosurgical forceps. However, the mechanism for assessing lesion transmurality provided by the present invention is believed useful in other contexts, including unipolar R-F ablation and R-F ablation using catheters or hand-held probes. The mechanism for assessing transmurality may also be of value in the context of other types of ablation systems, including those in which ablation occurs in conjunction with an induced rise in tissue temperature, such as those applying ablation energy in the form of microwave radiation, light (laser ablation) or heat (thermal ablation). The invention may also be useful in conjunction with other types of ablation, including cryo-ablation, ultrasound ablation and chemical ablation.
According to the present invention, assessment of transmurality of a lesion is accomplished by monitoring the depolarization signal amplitude in a local electrogram taken using electrodes located adjacent the tissue to be ablated. In the context of R-F ablation, measurement of electrogram amplitude may be done using the ablation electrodes or may be done using dedicated electrodes adjacent to the ablation electrodes. In the context of the other types of ablation discussed above, electrogram measurement would typically be accomplished by means of a dedicated set of measurement electrodes.
Following onset of application of ablation energy to heart tissue, the amplitude of a local electrogram measured with electrodes located adjacent tissue to be ablated first gradually drops and then stabilizes, indicating that the tissue being monitored has ceased making any contribution to the sensed electrogram. The amplitude drop (ΔEGM) or the following amplitude plateau “P” may be used alone or together as indicators of transmurality employed by the present invention. The amplitude drop may be compared to a pre-set value (ΔEGM? a). (The plateau “P” may be detected in response to a determination that the rate of amplitude change is less than a defined value over a series of amplitude measurements or over a defined duration (|dA/dt|=b). In some embodiments, detection of a rapid drop in amplitude (dA/dt=d) may be employed as an indicator that the ablation process is proceeding too quickly and may be employed to trigger a reduction in the power of applied ablation energy. In other embodiments, detection of an insufficiently rapid drop in amplitude (dA/dt=d) may be employed as an indicator that the ablation process is proceeding too slowly and may be employed to trigger an increase in the power of applied ablation energy.
In the context of R-F ablation, the invention is believed valuable in conjunction with an ablation device having multiple, individually activatable electrodes or electrode pairs to be arranged along a desired line of lesion. In this context, the mechanism for determining transmurality of lesions adjacent individual electrodes or pairs may be used to deactivate individual electrodes or electrode pairs, when the lesions in tissue adjacent these individual electrodes or electrode pairs are complete. This allows the creation of an essentially uniform lesion along the line of electrodes or electrode pairs, regardless of differences in tissue thickness adjacent the individual electrodes or electrode pairs. The invention is also believed useful in conjunction with assessment of transmurality of lesions produced by devices having only a single electrode or single electrode pair. Similar considerations apply to the use of the present invention in the contexts of other types of ablation as listed above.
In use, the hemostat is arranged so that the tissue to be ablated is located between the jaws 18 and 19, and pressure is applied in order to compress the tissue slightly between the jaws to ensure good electrical contact. All electrode pairs may be activated individually and may be individually deactivated when the lesions between the individual electrode pairs are completely transmural. Alternatively, electrode pairs could be activated sequentially, with one pair deactivated upon a detection of a complete lesion between the electrode pair, followed by activation of the next sequential electrode pair. Corresponding use of the invention in conjunction with a series of unipolar electrodes, for example corresponding to electrodes along one of the two jaws in conjunction with a remote ground plate or a similar series of individually activatable electrodes on a catheter or probe in conjunction with a ground plate is also possible.
Display 804 and controls 802 are connected to a digital microprocessor 800, which permits interface between the user and the remainder of the electrical components of the system. Microprocessor 800 operates under control of stored programming defining its operation including programming controlling its operation according to the present invention, as discussed in more detail below. Microprocessor 800 provides control outputs to and receives input signals from the remaining circuitry via address/data bus 806. In particular, the microprocessor 800 provides for monitoring of power, current, voltage, electrogram amplitude and temperature. As necessary, the microprocessor will provide this information to the display 804. Additionally, the microprocessor 800 permits the user to select the control mode (either temperature or power) and to input the power set point, temperature set point, and a timer set point to the system. The primary source of power for the radio-frequency generator may be a 12 V battery rated at 7.2 ampere-hours or the device may be AC powered. A back-up battery (not shown) such as a lithium cell may also be provided to provide sufficient power to the microprocessor 260 to maintain desired memory functions when the main power is shut off.
The power supply system as illustrated includes a desired number “M” of individually controllable R-F power supplies and receives temperature inputs from a desired number “N” of temperature sensing devices in the ablation device, illustrated schematically at 838 and receives electrogram amplitude inputs from a desired number “M” of electrogram monitoring circuits. Each R-F power supply includes a transformer (822, 824, 826), a power control circuit (810, 812, 814) and a power measurement circuit (816, 818, 820). A crystal-locked radio-frequency oscillator 264 generates the switching pulses, which drive both the power transformers (822, 824, 826) and the power controllers (810, 812, 814). Power controllers (810, 812, 814) may be analog controllers which operate by pulse-width modulation by comparing a power set point signal from microprocessor 800 with an actual power signal generated by a power measurement circuit (816, 818, 820), which may, for example, include a torroidal transformer coupled to the power output from the associated transformer (822, 824, 826). The power measurement circuits (816, 818, 820) multiply the output current and voltage and provide the resulting actual power signal to both the power controllers (810, 812, 814) and the microprocessor 800.
The R F power output of the transformers (822, 824, 826) is provided to interface board 808, and thereby is provided to the ablation electrode or electrodes on the ablation device 838. Separate analog comparator circuits (not illustrated) may also be provided for monitoring the output of the power measurement circuits (816, 818, 820), in order to shut-off current to the output transformers (822, 824, 826) if the power exceeds a limit, typically 55 watts. Power transformers (822, 824, 826) may include center taps, which receive the outputs of the power controllers (810, 812, 814). Secondary windings of the transformers (822, 824, 826) may provide for continuous monitoring of the applied voltage in order to permit the power calculations by power measurement circuits (816, 818, 820).
The illustrated power R-F generator system employs software controlled temperature processing, accomplished by micro processor 800, which receives the “N” temperature input signals from temperature measurement circuits (828, 830, 832), each of which are coupled to a corresponding temperature sensor in ablation device 838 by means of an electrical connector, illustrated schematically at 836 and interface circuit 834. If programmed to operate in the temperature controlled mode, processor 800 receives the “N” temperature signals and, based upon the indicated temperatures, defines power set points for each of the power control circuits (810, 812, 814), which in the manner described above control the power levels applied to electrodes on the catheter through interface 834. Processor 800 may also selectively enable or disable any of the “M” provided R-F power sup plies, in response to external control signals from controls 802 or in response to detected anomalous temperature conditions.
In addition to the circuitry as described above and disclosed in the Maguire, et al. '961 patent, the apparatus of
Individual electrogram amplitude measurements made by measurement circuits 843, 845 and 847 are provided to the address/data bus 806 and thence to microprocessor 800 for analysis to determine whether the behavior of the measured electrogram amplitude over time, indicates that the lesion associated with the measured amplitudes is completely transmural. As discussed in more detail below, a determination of transmurality may be made in response to detection of a defined drop in electrogram amplitude and/or a series of amplitude measurements that are relatively constant, over a desired period of time or over a defined number of successive amplitude measurements. In some embodiments, an abrupt drop in electrogram amplitude may also be employed to reduce the power level of ablation energy delivered to the tissue being monitored.
In cases in which an alternative ablation energy generation apparatus is employed, particularly those in which a rise in tissue temperature is induced, e.g. laser, microwave or thermal ablation, the R-F generation circuitry of
The flow chart of
After initialization at 200, the microprocessor 800 (
The flow chart of
After initialization at 300, the microprocessor 800 (
If the required drop is detected at 308, at 310, the microprocessor 800 employs the stored electrogram amplitude measurements to calculate dA/dt, which may, for example, be calculated based on net variation of electrogram amplitude over a series of 2 or 3 measurements. As discussed above in conjunction with detection of the required amplitude drop, averaged amplitude values may also be used to calculate dA/dt. The absolute value of dA/dt, i.e., |dA/dt| may employed to assess whether or not an electrogram amplitude plateau has been reached at 310, for example by verifying that a series of values of |dA/dt| are all (e.g. 3 of 3) or predominantly (e.g. 2 of 3) below a defined variability value “b”.
The processor continues to collect amplitude measurements and make calculations until such time as an amplitude plateau is recognized at 310 and a sufficient amplitude drop is recognized at 308. When both of these criteria have been met, the termination of application of ablation energy to the tissue being monitored then occurs at 312. The termination of ablation may occur concurrent with detection of the required drop or a preset delay thereafter to assure complete transmurality.
The flow chart of
After initialization at 400, the microprocessor 800 (
The processor continues to collect amplitude measurements until such time as an amplitude plateau is recognized at 410 and a sufficient time has elapsed at 412. When both of these criteria have been met, the termination of application of ablation energy to the tissue being monitored then occurs at 414. The termination of ablation may occur concurrent with detection of the required drop or a preset delay thereafter to assure complete transmurality.
After initialization at 600, all electrodes 1-X are activated at 602, meaning that ablation energy is provided to all electrodes and electrode pairs. The microprocessor measures the electrogram amplitude associated with a first electrode or electrode pair at 604 and then at 608 checks to see whether transmurality criteria are met for a first ablation electrode or electrode pair at 604, using the criteria discussed above in conjunction with any of
The overall operational methodology of
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|U.S. Classification||606/34, 607/122, 606/41, 600/508|
|International Classification||A61B5/04, A61B5/02, A61B18/14, A61B18/18, A61N1/00, A61N1/40, A61B18/12|
|Cooperative Classification||A61B18/1445, A61B2018/00702, A61B2018/00755, A61B2018/00875, A61N1/403, A61B5/04, A61B2018/00065, A61B2018/00363, A61B2018/1226, A61B2018/126, A61B2018/1253, A61B2018/00791, A61B2018/1472, A61B18/12, A61B2018/00654, A61B2018/00577, A61B2018/00779, A61B2018/1467, A61B2018/00839, A61B2218/002|
|European Classification||A61B18/12, A61B5/04, A61N1/40T, A61B18/14F2|
|Sep 22, 2009||FPAY||Fee payment|
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|Oct 18, 2013||FPAY||Fee payment|
Year of fee payment: 8